JP4191600B2

JP4191600B2 - Ophthalmic optical characteristic measuring device

Info

Publication number: JP4191600B2
Application number: JP2003526271A
Authority: JP
Inventors: 俊文三橋; 陽子広原; 尚不二門; 直之前田
Original assignee: Topcon Corp
Current assignee: Topcon Corp
Priority date: 2001-09-07
Filing date: 2002-08-09
Publication date: 2008-12-03
Anticipated expiration: 2022-08-09
Also published as: EP1437084A1; US20050073647A1; ATE499039T1; DE60239278D1; US7311402B2; WO2003022138A1; US20080123053A1; JPWO2003022138A1; US7677731B2; EP1437084B1

Abstract

A light source (10) emits a light beam of a wavelength in the near infrared region, illuminating a small area of the retinal of an eye using an illumination optical system (40) to be measured with the light beam from the light source. A light receiving optical system (20) receiving part of the reflected beam from the light source unit, reflected from the retina through a converting part of the reflected light beam into at least 17 substantially light beams. A light receiving section (23) for receiving the light beam directed by the light receiving optical system and generating a signal. A calculating unit for determining the wavefront aberration of the light beam entering the light receiving optical system.

Description

【技術分野】
【０００１】
本発明は、眼光学の特性を測定する眼光学特性測定装置に関する。
【背景技術】
【０００２】
ハルトマンシャック波面センサーは、眼球の波面収差を正確に測定できるため最近非常に注目されている。この波面センサーは、特に角膜屈折矯正手術のプランニングやフォローアップの目的で近い将来眼科手術の所要な装置となりうる。
【０００３】
ところで、波面センサーによる眼球波面収差の測定は、角膜形状測定による角膜波面収差の測定と比較して、水晶体などの眼球内部光学系の波面収差への影響が測定結果に含まれていることが大きく異なる。この機能によると、核白内障などで水晶体に屈折率異常がある場合や、円錐水晶体により水晶体の屈折面の形状が大きく歪んでいる場合などの検査が可能になる。
【０００４】
眼球光学系波面収差測定の目的としては、視機能の他覚的評価があげられる。視機能の評価としては、従来より自覚検査が他覚検査と比較して信頼できる測定法として認められてきた。特に波面センサーの前身と言えるオートレフラクトメーターに対して、自覚検査法であるレンズ交換法はゴールドスタンダードと言われているほどである。
【０００５】
波面センサーで測定した眼球波面収差と矯正視力やコントラストを比較すると、よく一致する場合と、例えば、高齢者を中心に一致しない場合がある。一致しない場合は、視力へ散乱が大きく影響を与えていることがある。
【発明の開示】
【発明が解決しようとする課題】
視機能に影響を及ぼす光学的要因として、波面収差と共に眼球光学系の散乱が考えられる。
眼光学特性の測定では、加齢や白内障等の場合、眼球光学系からの散乱が大きく、視機能の他覚的評価のために収差に加えて散乱の測定が必要である。波面収差の測定で定評のあるハルトマンシャック波面センサーの光学系による散乱の同時測定を可能にする装置が望まれている。一方、ハルトマンシャック波面センサーによる波面収差測定は、既に実用段階である。
【０００７】
本発明は、以上の点に鑑み、波面収差測定が主目的であるハルトマンシャック波面センサーで散乱測定を可能とし、散乱測定をすることで、視機能を正確に評価できる眼光学特性測定装置を提供することを目的とする。
また、本発明は、新たに、ハルトマンシャック波面センサーによる散乱測定法としてハルトマンイメージの背景光の散乱強度比（ＳＩＲ、ＳｃａｔｔｅｒＩｎｔｅｎｓｉｔｙＲａｔｉｏ）から散乱量を推定する散乱解析法を開発し、ハルトマンシャック波面センサーの光学系による散乱の同時測定を可能にする眼光学特性測定装置を提供することを目的とする。
【０００８】
また、本発明は、受光光学系に入射する光束の波面収差と、受光光の点像強度分布（ＰＳＦ）の関係の分布から、受光光学系に入射する光束の波面収差と、受光光束の散乱度合を測定することができる眼光学特性測定装置を提供することを目的とする。
また、本発明は、受光光学系に入射する光束の波面収差と、受光光束の散乱度合いと、受光光束のスポット径との関係の分布から、受光光学系に入射する光束の波面収差と、受光光束の散乱度合いが強いほど、又は受光光束のスポット径が大きいほど、白内障などの影響があるものと判断することができる眼光学特性測定装置を提供することを目的とする。
【課題を解決するための手段】
【０００９】
上記課題を解決するため、本発明の第１の解決手段によると、所定の波長の光束を発する光源部と、上記光源部からの光束で被検眼網膜上の微小な領域を照明するための照明光学系と、上記光源部からの光束が被検眼網膜から反射された反射光束の一部を、少なくとも実質的に１７本のビームに変換する変換部材を介して受光するための受光光学系と、上記受光光学系により導かれた受光光束を受光し、信号を形成する受光部と、上記受光部からの信号に基づき、上記受光光学系に入射する光束の波面収差と受光光束の散乱度合いを求める演算部を備えた眼光学特性測定装置が提供される。
【００１０】
また、本発明の第２の解決手段によると、所定の波長の光束を発する光源部と、上記光源部からの光束で被検眼網膜上の微小な領域を照明するための照明光学系と、上記光源部からの光束が被検眼網膜から反射された反射光束の一部を、少なくとも実質的に１７本のビームに変換する変換部材を介して受光するための受光光学系と、上記受光光学系により導かれた受光光束を受光し、信号を形成する受光部と、上記受光部からの信号に基づき、上記受光光学系に入射する光束の波面収差と受光光束のスポット径を求める演算部とを備えた眼光学特性測定装置が提供される。
【００１１】
また、本発明は、第１の解決手段の眼光学特性測定装置において、上記演算部は、上記受光光学系に入射する光束の波面収差と、受光光束の散乱度合いの関係の分布を求めることができる。さらに、本発明は、このような眼光学特性測定装置において、上記演算部は、求められた上記受光光学系に入射する光束の波面収差と、受光光束の散乱度合いが強いほど、白内障などの影響があるものと判断するように構成することができる。
【００１２】
また、本発明は、第２の解決手段の眼光学特性測定装置において、上記演算部は、上記受光光学系に入射する光束の波面収差と、受光光束のスポット径との関係の分布を求めることができる。さらに、本発明は、このような眼光学特性測定装置において、上記演算部は、求められた上記受光光学系に入射する光束の波面収差と、受光光束のスポット径が大きいほど、白内障などの影響があるものと判断するように構成することができる。
【００１３】
また、本発明は、第１の解決手段の眼光学特性測定装置において、上記演算部は、上記受光光学系に入射する光束の波面収差と、受光光束の散乱度合いと、受光光束のスポット径との関係の分布を求めることができる。さらに、本発明は、このような眼光学特性測定装置において、上記演算部は、求められた上記受光光学系に入射する光束の波面収差と、受光光束の散乱度合いが強いほど、又は受光光束のスポット径が大きいほど、白内障などの影響があるものと判断するように構成することができる。
さらに、本発明は、演算部により求められた分布、判断結果等を表示する表示部又はそれらを外部に出力する出力部をさらに備えるようにしてもよい。
さらに、本発明の第３の解決手段によると、所定の波長の光束を発する光源部と、
上記光源部からの光束で被検眼網膜上の微小な領域を照明するための照明光学系と、
上記光源部からの光束が被検眼網膜から反射された反射光束の一部を、少なくとも実質的に１７本のビームに変換する変換部材を介して受光するための受光光学系と、
上記受光光学系により導かれた受光光束を受光し、信号を形成する受光部と、
上記受光部からの信号に基づき、上記受光光学系に入射する光束の波面収差から求められた点像強度分布と受光光束の実測されたスポット径を求める演算部とを備えた眼光学特性測定装置が提供される。
【発明を実施するための最良の形態】
【００１４】
以下、図面を用いて本発明の実施の形態を詳細に説明する。
１．眼光学特性測定の原理説明
図１は、本発明に関する眼光学特性測定装置の概略光学系１００を示す図である。
【００１５】
眼光学特性測定装置の光学系１００は、例えば、対象物である被測定眼６０の光学特性を測定する装置であって、第１照明光学系１０と、第１受光光学系２０と、第２受光光学系３０と、共通光学系４０と、調整用光学系５０と、第２照明光学系７０と、第２送光光学系８０とを備える。なお、被測定眼６０については、図中、網膜６１、角膜６２が示されている。
【００１６】
第１照明光学系１０は、例えば、第１波長の光束を発するための第１光源部１１と、集光レンズ１２とを備え、第１光源部１１からの光束で被測定眼６０の網膜（眼底）６１上の微小な領域を、その照明条件を適宜設定できるように照明するためのものである。なお、ここでは、一例として、第１光源部１１から発せられる照明用の光束の第１波長は、赤外域の波長（例えば、７８０ｎｍ）である。これに限定されず、所定の波長の照明光束でよい。
【００１７】
また、第１光源部１１は、空間コヒーレンスが大きく、時間コヒーレンスが小さいものが望ましい。ここでは、第１光源部１１は、例えば、スーパールミネッセンスダイオード（ＳＬＤ）であって、輝度の高い点光源を得ることができる。
なお、第１光源部１１は、ＳＬＤに限られるものではなく、例えば、空間コヒーレンス、時間コヒーレンスが大きいレーザー等であっても、以下に述べるロータリープリズムとの組合せることにより利用することができる。さらに、空間コヒーレンス、時間コヒーレンスが小さいＬＥＤであっても、光量さえ十分であれば、例えば、光路の光源の位置にピンホール等を挿入することで、利用することができる。
また、網膜からの反射光の不均一な特性を均一にするために、楔形のロータリープリズム（Ｄプリズム）１６を照明光学系に挿入する。ロータリープリズムの回転により、眼底上の照明部分が操作されるため、眼底からの反射光が均一になり、受光部の受光光束（点像）が均一になるようにすることができる。
【００１８】
第１受光光学系２０は、例えば、コリメートレンズ２１と、被測定眼６０の網膜６１から反射して戻ってくる光束（第１光束）の一部を、少なくとも、１７本のビームに変換する変換部材であるハルトマン板２２と、このハルトマン板２２で変換された複数のビームを受光するための第１受光部２３とを備え、第１光束を第１受光部２３に導くためのものである。また、ここでは、第１受光部２３は、リードアウトノイズの少ないＣＣＤが採用されているが、ＣＣＤとしては、例えば、一般的な低ノイズタイプ、測定用の１０００＊１０００素子の冷却ＣＣＤ等、適宜のタイプのものを適用することができる。
【００１９】
第２照明光学系７０は、第２光源７２と、プラチドリング７１を備える。なお、第２光源７２を省略することもできる。図２に、プラチドリングの構成図の一例を示す。プラチドリング（ＰＬＡＣＩＤＯ’ＳＤＩＳＣ）７１は、図示のように、複数の同心輪帯からなるパターンの指標を投影するためのものである。なお、複数の同心輪帯からなるパターンの指標は、所定のパターンの指標の一例であり、他の適宜のパターンを用いることができる。そして、後述するアライメント調整が完了した後、複数の同心輪帯からなるパターンの指標を投影することができる。
【００２０】
第２送光光学系８０は、例えば、後述するアライメント調整及び座標原点、座標軸の測定・調整を主に行うものであって、第２波長の光束を発するための第２光源部３１と、集光レンズ３２と、ビームスプリッター３３を備える。
【００２１】
第２受光光学系３０は、集光レンズ３４、第２受光部３５を備える。第２受光光学系３０は、第２照明光学系７０から照明されたプラチドリング７１のパターンが、被測定眼６０の前眼部又は角膜６２から反射して戻ってくる光束（第２光束）を、第２受光部３５に導く。また、第２光源部３１から発せられ被測定眼６０の角膜６２から反射し、戻ってくる光束を第２受光部３５に導くこともできる。なお、第２光源部３１から発せられる光束の第２波長は、例えば、第１波長（ここでは、７８０ｎｍ）と異なると共に、長い波長を選択できる（例えば、９４０ｎｍ）。
【００２２】
共通光学系４０は、第１照明光学系１０から発せられる光束の光軸上に配され、第１及び第２照明光学系１０及び７０、第１及び第２受光光学系２０及び３０、第２送光光学系８０等に共通に含まれ得るものであり、例えば、アフォーカルレンズ４２と、ビームスプリッター４３、４５と、集光レンズ４４とを備える。また、ビームスプリッター４３は、第２光源部３１の波長を被測定眼６０に送光（反射）し、被測定眼６０の網膜６１から反射して戻ってくる第２光束を反射し、一方、第１光源部１１の光束を透過するようなミラー（例えば、偏光ビームスプリッター）で形成される。ビームスプリッター４５は、第１光源部１１の波長を被測定眼６０に送光（反射）し、被測定眼６０の網膜６１から反射して戻ってくる第１光束を、透過するようなミラー（例えば、ダイクロミックミラー）で形成される。このビームスプリッター４３、４５によって、第１及び２光束が、互いに他方の光学系に入りノイズとなることがない。
【００２３】
調整用光学系５０は、例えば、後述する作動距離調整を主に行うものであって、第３光源部５１と、第４光源部５５と、集光レンズ５２、５３と、第３受光部５４を備え、主に作動距離調整を行うものである。
【００２４】
つぎに、アライメント調整について説明する。アライメント調整は、主に、第２受光光学系３０及び第２送光光学系８０により実施される。
【００２５】
まず、第２光源部３１からの光束は、集光レンズ３２、ビームスプリッター３３、４３、アフォーカルレンズ４２を介して、対象物である被測定眼６０を略平行な光束で照明する。被測定眼６０の角膜６２で反射した反射光束は、あたかも角膜６２の曲率半径の１／２の点から射出したような発散光束として射出される。この発散光束は、アフォーカルレンズ４２、ビームスプリッター４３、３３及び集光レンズ３４を介して、第２受光部３５にスポット像として受光される。
【００２６】
ここで、この第２受光部３５上のスポット像を光軸上から外れている場合、眼光学特性測定装置本体を、上下左右に移動調整し、スポット像が光軸上と一致させる。このように、スポット像が光軸上と一致すると、アライメント調整は完了する。なお、アライメント調整は、被測定眼６０の角膜６２を第３光源部５１により照明し、この照明により得られた被測定眼６０の像が第２受光部３５上に形成されるので、この像を利用して瞳中心が光軸と一致するようにしてもよい。
【００２７】
つぎに、作動距離調整について説明する。作動距離調整は、主に、調整用光学系５０により実施される。
まず、作動距離調整は、例えば、第４光源部５５から射出された光軸付近の平行な光束を、被測定眼６０に向けて照射すると共に、この被測定眼６０から反射された光を、集光レンズ５２、５３を介して第３受光部５４で受光することにより行われる。また、被測定眼６０が適正な作動距離にある場合、第３受光部５４の光軸上に、第４光源部５５からのスポット像が形成される。一方、被測定眼６０が適正な作動距離から前後に外れた場合、第４光源部５５からのスポット像は、第３受光部５４の光軸より上又は下に形成される。なお、第３受光部５４は、第４光源部５５、光軸、第３受光部５４を含む面内での光束位置の変化を検出できればいいので、例えば、この面内に配された１次元ＣＣＤ、ポジションセンシングデバイス（ＰＳＤ）等を適用できる。
【００２８】
つぎに、第１照明光学系１０と第１受光光学系２０との位置関係を概略的に説明する。
第１受光光学系２０には、ビームスプリッター４５が挿入されており、このビームスプリッター４５によって、第１照明光学系１０からの光は、被測定眼６０に送光されると共に、被測定眼６０からの反射光は、透過される。第１受光光学系２０に含まれる第１受光部２３は、変換部材であるハルトマン板２２を通過した光を受光し、受光信号を生成する。
【００２９】
また、第１光源部１１と被測定眼６０の網膜６１とは、共役な関係を形成している。被測定眼６０の網膜６１と第１受光部２３とは、共役である。また、ハルトマン板２２と被測定眼６０の瞳孔とは、共役な関係を形成している。さらに、第１受光光学系２０は、被測定眼６０の前眼部である角膜６２、及び瞳孔と、ハルトマン板２２と略共役な関係を形成している。すなわち、アフォーカルレンズ４２の前側焦点は、被測定眼６０の前眼部である角膜６２及び瞳孔と略一致している。また、光軸に対し傾斜しているロータリープリズム１６の面は、瞳孔と略共役位置に配置されている。
【００３０】
また、第１照明光学系１０と第１受光光学系２０は、第１光源部１１からの光束が、集光する点で反射されたとして、第１受光部２３での反射光による信号ピークが最大となるように、連動して移動する。具体的には、第１照明光学系１０と第１受光光学系２０は、第１受光部２３での信号ピークが大きくなる方向に移動し、信号ピークが最大となる位置で停止する。これにより、第１光源部１１からの光束は、被測定眼６０上で集光する。
【００３１】
また、レンズ１２は、光源１１の拡散光を平行光に変換する。絞り１４は、眼の瞳、あるいはハルトマンプレート２１と光学的に共役の位置にある。絞り１４は、径がハルトマンプレート２１の有効範囲より小さく、いわゆるシングルパスの収差計測（受光側だけに目の収差が影響する方法）が成り立つ様になっている。レンズ１３は、上記を満たすために、実光線の眼底共役点を前側焦点位置に、さらに、眼の瞳との共役関係を満たすために、後側焦点位置が絞り１４と一致するように配置されている。
【００３２】
また、光線１５は、光線２４とビームスプリッター４５で共通光路になった後は、近軸的には、光線２４と同じ進み方をする。但し、シングルパス測定のときは、それぞれの光線の径は違い、光線１５のビーム径は、光線２４に比べ、かなり細く設定される。具体的には、光線１５のビーム径は、例えば、眼の瞳位置で１ｍｍ程度、光線２４のビーム径は、７ｍｍ程度になることもある（なお、図中、光線１５のビームスプリッター４５から眼底６１までは省略している）。
【００３３】
つぎに、変換部材であるハルトマン板２２について説明する。
第１受光光学系２０に含まれるハルトマン板２２は、反射光束を複数のビームに変換する波面変換部材である。ここでは、ハルトマン板２２には、光軸と直交する面内に配された複数のマイクロフレネルレンズが適用されている。また、一般に、測定対象部（被測定眼６０）について、被測定眼６０の球面成分、３次の非点収差、その他の高次収差までも測定するには、被測定眼６０を介した少なくとも１７本のビームで測定する必要がある。
【００３４】
また、マイクロフレネルレンズは、光学素子であって、例えば、波長ごとの高さピッチの輪帯と、集光点と平行な出射に最適化されたブレーズとを備える。ここでのマイクロフレネルレンズは、例えば、半導体微細加工技術を応用した８レベルの光路長差を施したもので、高い集光率（例えば、９８％）を達成している。
【００３５】
また、被測定眼６０の網膜６１からの反射光は、アフォーカルレンズ４２、コリメートレンズ２１を通過し、ハルトマン板２２を介して、第１受光部２３上に集光する。したがって、ハルトマン板２２は、反射光束を少なくとも、１７本以上のビームに変換する波面変換部材を備える。
【００３６】
図３は、本発明に関する眼光学特性測定装置の概略電気系２００を示すブロック図である。眼光学特性測定装置に関する電気系２００は、例えば、演算部２１０と、制御部２２０と、表示部２３０と、メモリ２４０と、第１駆動部２５０及び第２駆動部とを備える。
【００３７】
演算部２１０は、第１受光部２３から得られる受光信号（４）、第２受光部３５から得られる受光信号（７）、第３受光部５４から得られる受光信号（１０）を入力すると共に、座標原点、座標軸、座標の移動、回転、全波面収差、角膜は面収差、ゼルニケ係数、収差係数、Ｓｔｒｅｈｌ比、白色光ＭＴＦ、ランドルト環パターン等を演算する。また、このような演算結果に応じた信号を、電気駆動系の全体の制御を行う制御部２２０と、表示部２３０と、メモリ２４０とにそれぞれ出力する。なお、演算２１０の詳細は後述する。
【００３８】
制御部２２０は、演算部２１０からの制御信号に基づいて、第１光源部１１の点灯、消灯を制御したり、第１駆動部２５０及び第２駆動部２６０を制御するものであり、例えば、演算部２１０での演算結果に応じた信号に基づいて、第１光源部１１に対して信号（１）を出力し、プラチドリング７１に対して信号（５）を出力し、第２光源部３１に対して信号（６）を出力し、第３光源部５１に対して信号（８）を出力し、第４駆動部に対して信号（９）を出力し、さらに、第１駆動部２５０及び第２駆動部２６０に対して信号を出力する。
【００３９】
第１駆動部２５０は、例えば、演算部２１０に入力された第１受光部２３からの受光信号（４）に基づいて、第１照明光学系１０全体を光軸方向に移動させるものであり、図示しない適宜のレンズ移動手段に対して信号（２）を出力すると共に、このレンズ移動手段を駆動する。これにより、第１駆動手段２５０は、第１照明光学系１０の移動、調節を行うことができる。
【００４０】
第２駆動手段２６０は、例えば、演算部２１０に入力された第１受光部２３からの受光信号（４）に基づいて、第１受光光学系２０全体を光軸方向に移動させるものであり、図示しない適宜のレンズ移動手段に対して信号（３）を出力すると共に、このレンズ移動手段を駆動する。これにより、第２駆動手段２６０は、第１受光光学系２０の移動、調節を行うことができる。
【００４１】
図４に、本発明の眼特性測定装置の演算部に関する詳細構成図を示す。演算部２１０は、測定部１１１、解析部１１１’、座標設定部１１２、アライメント制御部１１３、マーカー設置部１１４、入出力部１１５、変換部１１６を備える。
【００４２】
第１受光部２３は、被検眼眼底から反射して戻ってくる受光光束から第１受光信号を形成し、測定部１１１に導く。第２受光部３５は、被検眼前眼部の特徴部分及び／又は被検眼前眼部に形成されたマーカーに関する情報を含む受光光束から前眼部の情報を含む第２受光信号を形成し、測定部１１１及び座標設定部１１２に導く。
【００４３】
測定部１１１は、第１受光部からの第１受光信号に基づき、被検眼の屈折力又は角膜形成を含む光学特性を求める。また、測定部１１１は、受光光束のスポット径および受光光束の散乱度合いを求めるための解析部１１１’に第１受光信号を送る。なお、解析部１１１’は、第１受光部２３から直接第１受光信号を入力するように構成されてもよい。解析部１１１’の詳細については後述する。測定部１１１は、特に、第１受光部２３からの第１受光信号に基づき、眼光学特性測定を行う。また、測定部１１１は、特に、第２受光部３５からの第２受光信号に基づき、角膜トポグラフィー測定を行う。また、測定部１１１は、収差結果の演算、また必要に応じてアブレーション量を演算し、その演算結果を入出力部１１５を介して手術装置に出力する。
【００４４】
図５は、第１受光部２３により受光された画像の一部を拡大した図である。図（Ａ）が円錐角膜眼、図（Ｂ）が白内障眼の場合のハルトマン像の一例である。第１受光部２３により受光されたハルトマン像は、例えば、被測定眼からの反射光に基づいた画像であって、この反射光がハルトマン板２２を介して概ね外側に拡散した光束として第１受光部２３上に受光された場合での複数の領域点（図中、円状、楕円状等）を含む。この例のハルトマン像の光信号は、電気信号に変換され、上述の第１信号として解析部１１１’に入力される（又は、取り込まれる）。
【００４５】
このように、ハルトマンシャック波面センサーからの情報としては、次のようなものが含まれる。
・点像の重心から波面（古典的な収差計測）
・点像のボケ具合から局所的な情報（局所的な散乱計測）
また、散乱の多い眼については、ハルトマン像に波面収差のみからでは説明することのできない像のボケが観察される。また、測定で得られたハルトマン像と波面収差から復元されたハルトマン像とを比較することにより、散乱量を推定することが考えられる。
【００４６】
解析部１１１’では、この複数の領域点は受光光束の一つと捉え、受光光束のスポット径乃至受光光束の光量の最大値と最小値との比、すなわち受光光束の散乱度合いを求める。解析部１１１’は、受光光学系に入射する光束の波面収差と、受光光束の散乱度合いの関係を示す分布を求める。また、受光光学系に入射する光束の波面収差と、受光光束のスポット径との関係を示す分布を求める。なお、解析部１１１’は受光光学系に入射する光束の波面収差と、受光光束の散乱度合いと、受光光束のスポット径との相関関係について分布を求めるものであるので、上述した分布に限定されない。
【００４７】
解析部１１１’は、受光光学系に入射する光束の波面収差から、波動光学的計算による点像強度分布（ＰＳＦ）をもとめ、これと、受光光束の径、つまり画像からの強度を実測して求めた、点像強度分布（ＰＳＦ）を比較する計算機能を有する。たとえば、点像を含む四角形領域（その辺の長さはおおよそ点像の間隔に等しく、この領域には点像一つが通常含まれる）内での、最大値、最小値の中間値での面積、あるいは、幅などを比較できるようになっていることもある。
なお、解析部１１１’のいままで述べた解析は、ハルトマン像の特定の複数個の点像に対応していてもよく、この条件では、一回の測定の結果として、計算は、それぞれの点像を解析したり、実測して得られた値の平均値を利用することもある。
解析部１１１’は、求められた上記第１受光部である受光光学系に入射する光束の受光光束の散乱度合いが強いほど、白内障などの影響があるものと判断し、その旨表示部２４０に出力することができる。また、解析部１１１’は、求められた上記第１受光部である受光光学系に受光光束のスポット径が大きいほど、白内障などの影響があるものと判断し、その旨表示部２４０に出力することができる。
【００４８】
なお、解析部１１１’による判断結果、解析結果等は、表示部２４０にデータ、表、グラフ、３次元表示、グラフィック表示等の各種様式で表示されたり、出力部によりＣＤ−ＲＯＭ、ＦＤ、ＭＯ等の記録媒体又は他の装置に出力されるようにしてもよい。
図６に、波面から点像強度分布を求める説明図を示す。
被検眼眼底から反射した光束の波面がハルトマン板を通過し、そのときの光束の傾斜からレンズレット内の波面収差ＲＭＳが求め、さらに点像強度分布ＰＳＦの半値部分の面積などのファクターを求める。
なお、解析部１１１’は、散乱係数を次式のように求めることができる。
【００４９】
【数１】

【００５０】
・Ｉｎｄｅｘ：散乱係数（散乱指標ともいう）
・Ａ：ＰＳＦの半値部分の面積（平均）
・ＲＭＳ_SL：レンズレット部分での波面収差（平均）
・ａ：非白内障眼測定により求める定数
・ｃ：測定装置の散乱校正定数
なお、ａ、ｃは図７で、円錐角膜眼と正常眼を使ってもとめた、回帰直線の係数である。この場合は、ａ：１次の係数は２８．８９４、ｃ：定数項は８．６６２３である。
実際の解析では、ハルトマン像の複数の点像について、面積Ａをもとめ、これを、上記の式で処理したものを、平均して一回の測定の結果とすることもある。
この散乱係数は、各レンズレットの各種ファクターを用いて、各レンズレット毎に求められる。
点像の画像と点像強度との関係は、図９に示す関係にある。この際、光量と出力の関係を示すガンマ値は１になるようなＣＣＤを採用しておれば、ＰＳＦの強度分布はＣＣＤのデジタルカウント（コンピュータカウント）に比例するので、測定が簡単である。ここで、点像を中心とした０．６ｍｍ角の四角形ないで、最低、最高強度をもとめ、これからマイケルソンコントラスト比をもとめることも可能であるし、最低と最高強度の中間点の面積を求めることも可能である。
また、波面収差ＲＭＳ_ＳＬの代わりに、図６の点像強度分布（ＰＳＦ）を波面収差から計算して求め、これを、上記の実測のＰＳＦと比較する方法も考えられる。
この方法を使った場合は、正常眼と円錐角膜など、散乱が少ない眼を使った、校正の必要がなくなり、結果の信頼性が増す。一方、波面収差とＰＳＦを比較する前の方法では、計算によりＰＳＦを計算する手間がないので、全体の処理時間をかなり短くすることができる。
【００５１】
座標設定部１１２は、第１又は第２受光信号に含まれる被検眼瞳に対応する第１及び第２座標系の信号を、それぞれ基準座標系の信号に変換する。座標設定部１１２は、第１及び第２座標系の各信号に基づき、瞳エッジと瞳中心を求める。
【００５２】
また、座標設定部１１２は、被検眼前眼部の特徴信号を含む第２受光信号に基づき、座標原点及び座標軸の向きを決定する。また、座標設定部１１２は、第２受光信号中の被検眼前眼部の特徴信号の少なくともいずれか１つに基づき、座標原点、座標軸の回転や移動を求め、測定データと座標軸の関係付けを行う。なお、特徴部分は、瞳位置、瞳中心、角膜中心、虹彩位置、虹彩の模様、瞳の形状、リンバス形状の少なくとも一つを含むものである。例えば、座標設定部１１２は、瞳中心、角膜中心等の座標原点を設定する。座標設定部１１２は、第２受光信号に含まれる被検眼前眼部の特徴部分の像に対応する特徴信号に基づき座標系を形成する。また、座標設定部１１２は、第２受光信号に含まれる被検眼に設けられたマーカーについてのマーカー信号及び被検眼前眼部についての信号に基づき座標系を形成する。座標設定部１１２は、マーカー信号を含む第２受光信号に基づき、座標原点及び座標軸の向きを決定することができる。座標設定部１１２は、第２受光信号中のマーカー信号に基づいて、座標原点を求め、第２受光信号中の被検眼前眼部の特徴信号の少なくともいずれか１つに基づき、座標軸の回転や移動を求め、測定データと座標間の関係付けを行うことができる。または、座標設定部１１２は、第２受光信号中の前眼部についての特徴信号の少なくともいずれか１つに基づき座標原点を求め、第２受光信号中のマーカー信号に基づいて座標軸の回転や移動を求め、測定データと座標軸の関係付けを行うようにしてもよい。または、座標設定部１１２は、第２受光信号中の被検眼前眼部の特徴信号の少なくともいずれか１つに基づき、座標原点、座標軸の回転や移動を求め、測定データと座標軸の関係付けを行うようにしてもよい。
【００５３】
変換部１１６は、測定部１１１により求められた被検眼の第１及び第２光学特性を、前記座標設定部により形成された各基準座標系により関係つけて合成する。また、変換部１１６は、座標設定部１１２が求めた瞳中心を原点とすることにより基準座標系に変換する。
【００５４】
第１照明光学系と、第１受光光学系２０と、第２受光光学系３０と、共通光学系４０と、調整用光学系５０と、第２照明光学系７０と、第２送光光学系８０等のいずれかひとつ又は複数又は全ては、適宜光学系１００のアライメント部に掲載される。アライメント制御部１１３は、第２受光部により得られた第２受光信号に基づく座標設定部１１２の演算結果に従い、被検眼の動きに応じてこのアライメント部を移動可能とする。マーカー設置部１１４は、座標設定部１１２により設定された座標系に基づき被検眼前眼部にこの座標系に関連付けられたマーカーを形成する。入出力部１１５は、測定部又は座標設定部からの、収差量、座標原点、座標軸の回転、移動、アブレーション量等のデータや演算結果を手術装置に出力するためのインタフェースである。表示部２４０は、測定部１１１により求められた被検眼の光学特性を、上記座標設定部により形成された座標系との関係で表示を行う。
【００５５】
手術装置３００は、手術制御部１２１、加工部１２２、メモリ部１２３を含む。手術制御部１２１は、加工部１２２を制御し、角膜切削等の手術の制御を行う。加工部１２２は、角膜切削等の手術のためのレーザを含む。手術メモリ部１２３は、切削に関するデータ、モノグラム、手術計画等の手術のためのデータが記憶されている。
【００５６】
次に、図７に、本実施の形態に係る眼光学特性測定装置による実験結果の図（１）を示す。本発明の実施の形態には、眼光学特性の測定についての確認のため、正常眼９眼、円錐角膜眼２４眼、白内障眼１７眼の測定を行ない半値幅を求めた。なお、図中、正常眼（ｎｏｒｍａｌ）はひし形（◆）、円錐角膜眼（ｋｅｒａｔｏｃｏｎｕｓ）は四角（■）、白内障眼（ｃａｔａｒａｃｔ）は三角（▲）で示している。
【００５７】
測定部１１１又は解析部１１１’は、第１受光信号（４）からの出力結果を所定の解析方法で解析する。すなわち、受光したレーザ光のぼけを散乱光と考え、受光光束のスポット径の大きさを基にした半値幅（ｓｑｕａｒｅｒｏｏｔｏｆａｒｅａｆｏｒａｐｏｔｓ）、または受光光束の最大受光量に対する最小受光量の比、すなわち散乱強度比（ｍｉｎｉｍｕｍｉｎｔｅｎｓｉｔｙ／ｍａｘｉｍｕｍｉｎｔｅｎｓｉｔｙ、散乱係数）を求める。また、測定部１１１又は解析部１１１’は、受光光学系で求められた第１受光部２３に入射する波面収差の位相（標準偏差）に対する、受光光束のスポット径の分布（図６）または受光光束の散乱強度比の分布を作成する。
【００５８】
なお、白内障眼については、この近似した直線から外れることにより、円錐角膜眼と区別して識別することができる。すなわち、求められた直線近似を基にして白内障眼の疑いのある被検者とを判別し、手術・治療の判断材料に用いることができる。
【００５９】
図８に、本実施の形態に係る眼光学特性測定装置による実験結果の図（２）を示す。
この図は、図７の半値幅から[数１]による補正を加えたものである。縦軸は半値幅から[数１]にレンズレットの波面収差を代入して求めた値を減算することによって得られた量である。非白内障眼では求めた値がほぼ横並びになる。白内障眼、または散乱の大きい目ではこの値が大きくなる。また、散乱を無視できる模型眼を測定し、この測定値でさらに校正をかけて、散乱量の予測をより正確にすることも考えられる。ここで、用いた方法は、水晶体散乱の測定に向いているが、網膜散乱などの測定に応用することも考えられる。
【００６０】
解析の結果、一例として、正常眼でＳＩＲ（散乱強度比）＝０．４６０±０．０６７、円錐角膜眼でＳＩＲ＝０．４９５±０．０９８、白内障眼でＳＩＲ＝０．６６７±０．１４８となった（ＡＮＯＶＡ（分散分析）、Ｐ＜０．０１）。また、散乱係数は、正常眼で２．６１±０．７０、円錐角膜眼で３．３８±２．７３、白内障眼で１０．１３±７．２５であった。また、正常眼と円錐角膜眼の間には有意差がなかったが（Ｐ＜０．１２２）、正常眼と白内障眼、円錐角膜眼と白内障眼間には有意差があった（Ｐ＜０．０１）。なお、解析法の有効性を確認するために散乱の少ない正常眼９眼と円錐角膜眼２４眼、散乱の大きい白内障眼１７眼を測定した。
【００６１】
これにより、ハルトマンシャック波面センサーによる散乱量の測定の可能性が示唆された。今後、視機能と比較可能な評価基準を検討すると共に臨床上の有効性を確認する。
【産業上の利用可能性】
【００６２】
本発明によると、波面収差測定が主目的であるハルトマンシャック波面センサーで散乱測定を可能とし、散乱測定をすることで、視機能を正確に評価できる眼光学特性測定装置を提供することができる。
【００６３】
また、本発明によると、新たに、ハルトマンシャック波面センサーによる散乱測定法としてハルトマンイメージの背景光の散乱強度比（ＳＩＲ、ＳｃａｔｔｅｒＩｎｔｅｎｓｉｔｙＲａｔｉｏ）から散乱量を推定する散乱解析法を開発し、ハルトマンシャック波面センサーの光学系による散乱の同時測定を可能にする眼光学特性測定装置を提供することができる。
【００６４】
また、本発明によると、受光光学系に入射する光束の波面収差と、受光光束の散乱度合いの関係の分布から、受光光学系に入射する光束の波面収差と、受光光束の散乱度合いが強いほど、白内障の影響があるものと判断することができる眼光学特性測定装置を提供することができる。
また、本発明によると、受光光学系に入射する光束の波面収差と、受光光束の散乱度合いと、受光光束のスポット径との関係の分布から、受光光学系に入射する光束の波面収差と、受光光束の散乱度合いが強いほど、又は受光光束のスポット径が大きいほど、白内障の影響があるものと判断することができる眼光学特性測定装置を提供することができる。
【図面の簡単な説明】
【００６５】
【図１】本発明に関する眼光学特性測定装置の概略光学系１００を示す図。
【図２】プラチドリングの構成図。
【図３】本発明に関する眼光学特性測定装置の概略電気系２００を示すブロック図。
【図４】本発明の眼特性測定装置の演算部に関する詳細構成図。
【図５】第１受光部２３により受光された画像の一部を拡大した図。
【図６】波面から点像強度分布を求める説明図。
【図７】本実施の形態に係る眼光学特性測定装置による実験結果の図（１）。
【図８】本実施の形態に係る眼光学特性測定装置による実験結果の図（２）。
【図９】点像の画像と点像強度を示す説明図。【Technical field】
[0001]
The present invention relates to an eye optical property measuring apparatus that measures eye optical properties.
[Background]
[0002]
The Hartmann Shack wavefront sensor has recently received much attention because it can accurately measure the wavefront aberration of the eyeball. This wavefront sensor can be a necessary device for ophthalmic surgery in the near future, especially for planning and follow-up of corneal refractive surgery.
[0003]
By the way, the measurement of ocular wavefront aberration by a wavefront sensor has a greater effect on the wavefront aberration of the intraocular optical system such as the crystalline lens than the measurement of corneal wavefront aberration by corneal shape measurement. Different. According to this function, it is possible to inspect when the crystalline lens has a refractive index abnormality due to nuclear cataract or the like, or when the shape of the refractive surface of the crystalline lens is greatly distorted by the conical crystalline lens.
[0004]
The objective of the eyeball optical system wavefront aberration measurement is objective evaluation of visual function. For the evaluation of visual function, the subjective test has been accepted as a reliable measurement method compared with the objective test. In contrast to the autorefractometer, which can be said to be the predecessor of wavefront sensors, the lens replacement method, which is a subjective examination method, is said to be the gold standard.
[0005]
When eyeball wavefront aberration measured by the wavefront sensor is compared with corrected visual acuity and contrast, there are cases where they match well, for example, they do not coincide mainly with elderly people. If they do not match, scattering may have a significant effect on visual acuity.
DISCLOSURE OF THE INVENTION
[Problems to be solved by the invention]
As an optical factor affecting the visual function, the scattering of the eyeball optical system can be considered together with the wavefront aberration.
In the measurement of ocular optical characteristics, in the case of aging, cataracts, etc., scattering from the eyeball optical system is large, and in addition to aberrations, measurement of scattering is necessary for objective evaluation of visual function. There is a demand for an apparatus that enables simultaneous measurement of scattering by the optical system of the Hartmann Shack wavefront sensor, which has a well-established measurement of wavefront aberration. On the other hand, wavefront aberration measurement using a Hartmann Shack wavefront sensor is already in practical use.
[0007]
In view of the above points, the present invention provides an ophthalmic optical characteristic measuring device that enables scatter measurement with a Hartmann Shack wavefront sensor, whose main purpose is wavefront aberration measurement, and can accurately evaluate visual function by performing scatter measurement. The purpose is to do.
The present invention also newly developed a scattering analysis method for estimating the amount of scattering from a scattering intensity ratio (SIR) of a background light of a Hartmann image as a scattering measurement method using a Hartmann Shack wavefront sensor, and a Hartmann Shack wavefront. An object of the present invention is to provide an eye optical property measuring apparatus that enables simultaneous measurement of scattering by an optical system of a sensor.
[0008]
Further, the present invention is based on the distribution of the wavefront aberration of the light beam incident on the light receiving optical system and the point image intensity distribution (PSF) of the received light, and the wavefront aberration of the light beam incident on the light receiving optical system and the scattering of the received light beam. It is an object of the present invention to provide an eye optical characteristic measuring apparatus capable of measuring the degree.
In addition, the present invention provides the wavefront aberration of the light beam incident on the light receiving optical system, the distribution of the wavefront aberration of the light beam incident on the light receiving optical system, the degree of scattering of the light received light beam, and the spot diameter of the light receiving light beam, It is an object of the present invention to provide an ophthalmic optical characteristic measuring apparatus that can determine that the greater the degree of light beam scattering or the larger the spot diameter of a received light beam, the greater the effect of cataracts.
[Means for Solving the Problems]
[0009]
In order to solve the above-described problem, according to the first solution of the present invention, a light source unit that emits a light beam having a predetermined wavelength and illumination for illuminating a minute region on the retina of the eye to be examined with the light beam from the light source unit. An optical system, and a light receiving optical system for receiving a part of the reflected light beam reflected from the retina of the eye to be examined via a conversion member that converts the light beam from the light source unit into at least substantially 17 beams; Based on the signal from the light receiving unit that receives the received light beam guided by the light receiving optical system and forms a signal and the signal from the light receiving unit, the wavefront aberration of the light beam incident on the light receiving optical system and the degree of scattering of the received light beam are obtained. An ophthalmic optical characteristic measuring apparatus including a calculation unit is provided.
[0010]
According to the second solving means of the present invention, a light source unit that emits a light beam of a predetermined wavelength, an illumination optical system for illuminating a minute region on the eye retina with the light beam from the light source unit, and A light receiving optical system for receiving a part of the reflected light beam reflected from the retina of the eye to be examined through a conversion member that converts the light beam from the light source unit into at least substantially 17 beams, and the light receiving optical system. A light receiving unit that receives the received light beam and forms a signal; and a calculation unit that calculates a wavefront aberration of the light beam incident on the light receiving optical system and a spot diameter of the light beam based on a signal from the light receiving unit. An ophthalmic optical property measuring apparatus is provided.
[0011]
In the eye optical characteristic measuring apparatus according to the first aspect of the present invention, the calculation unit obtains a distribution of a relationship between a wavefront aberration of a light beam incident on the light receiving optical system and a degree of scattering of the light received light beam. it can. Furthermore, the present invention provides an apparatus for measuring optical characteristics of an eye in which the calculation unit has an effect of cataract as the wavefront aberration of the light beam incident on the light receiving optical system and the degree of scattering of the received light beam are stronger. It can be configured to determine that there is.
[0012]
In the ophthalmic optical characteristic measuring apparatus according to the second aspect of the present invention, the calculation unit obtains a distribution of a relationship between a wavefront aberration of a light beam incident on the light receiving optical system and a spot diameter of the light received light beam. Can do. Furthermore, the present invention provides an apparatus for measuring optical characteristics of an eye, wherein the calculation unit has a larger effect on the wavefront aberration of the light beam incident on the light receiving optical system and the effect of cataracts as the spot diameter of the light received light beam is larger. It can be configured to determine that there is.
[0013]
In the ophthalmic optical characteristic measuring apparatus according to the first aspect of the present invention, the calculation unit includes a wavefront aberration of a light beam incident on the light receiving optical system, a degree of scattering of the received light beam, and a spot diameter of the received light beam. The distribution of the relationship can be obtained. Furthermore, in the eye optical characteristic measuring apparatus according to the present invention, the calculation unit may increase the wavefront aberration of the light beam incident on the received light receiving optical system and the degree of scattering of the received light beam, or the received light beam. It can be configured that the larger the spot diameter is, the more likely it is to have an influence such as cataract.
Furthermore, the present invention may further include a display unit that displays a distribution obtained by the calculation unit, a determination result, or the like, or an output unit that outputs them to the outside.
Furthermore, according to the third solution of the present invention, a light source unit that emits a light beam having a predetermined wavelength;
An illumination optical system for illuminating a minute region on the eye retina with the light flux from the light source unit;
A light receiving optical system for receiving a part of the reflected light beam reflected from the retina of the eye to be examined through a conversion member that converts the light beam from the light source unit into at least substantially 17 beams;
A light receiving portion for receiving a received light beam guided by the light receiving optical system and forming a signal;
An ophthalmic optical characteristic measuring apparatus comprising: a point image intensity distribution obtained from wavefront aberration of a light beam incident on the light receiving optical system based on a signal from the light receiving unit; and a calculation unit for obtaining an actually measured spot diameter of the received light beam. Is provided.
BEST MODE FOR CARRYING OUT THE INVENTION
[0014]
Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.
1. Explanation of the principle of ocular optical characteristics measurement
FIG. 1 is a diagram showing a schematic optical system 100 of an eye optical characteristic measuring apparatus according to the present invention.
[0015]
The optical system 100 of the eye optical characteristic measuring apparatus is an apparatus for measuring optical characteristics of the eye 60 to be measured, which is an object, for example, and includes a first illumination optical system 10, a first light receiving optical system 20, and a second The light receiving optical system 30, the common optical system 40, the adjustment optical system 50, the second illumination optical system 70, and the second light transmission optical system 80 are provided. In addition, about the to-be-measured eye 60, the retina 61 and the cornea 62 are shown in the figure.
[0016]
The first illumination optical system 10 includes, for example, a first light source unit 11 for emitting a light beam having a first wavelength, and a condensing lens 12, and the retina of the eye 60 to be measured with the light beam from the first light source unit 11. This is for illuminating a minute region on the (fundus) 61 so that the illumination conditions can be set as appropriate. Here, as an example, the first wavelength of the illumination light beam emitted from the first light source unit 11 is an infrared wavelength (for example, 780 nm). However, the present invention is not limited to this, and an illumination light beam having a predetermined wavelength may be used.
[0017]
The first light source unit 11 preferably has a large spatial coherence and a small temporal coherence. Here, the 1st light source part 11 is a super luminescence diode (SLD), for example, Comprising: It can obtain a point light source with high brightness | luminance.
The first light source unit 11 is not limited to the SLD, and for example, even a laser having a large spatial coherence and temporal coherence can be used by combining with a rotary prism described below. Furthermore, even an LED with small spatial coherence and temporal coherence can be used by inserting a pinhole or the like at the position of the light source in the optical path as long as the amount of light is sufficient.
Further, in order to make the non-uniform characteristic of the reflected light from the retina uniform, a wedge-shaped rotary prism (D prism) 16 is inserted into the illumination optical system. Since the illumination part on the fundus is operated by the rotation of the rotary prism, the reflected light from the fundus can be made uniform, and the received light beam (point image) of the light receiving unit can be made uniform.
[0018]
The first light receiving optical system 20 converts, for example, a part of a light beam (first light beam) reflected and returned from the collimator lens 21 and the retina 61 of the eye 60 to be measured into at least 17 beams. A Hartmann plate 22 as a member and a first light receiving unit 23 for receiving a plurality of beams converted by the Hartman plate 22 are provided to guide the first light flux to the first light receiving unit 23. Here, the first light receiving unit 23 is a CCD with low lead-out noise, but as the CCD, for example, a general low noise type, a cooling CCD of 1000 * 1000 elements for measurement, etc. An appropriate type can be applied.
[0019]
The second illumination optical system 70 includes a second light source 72 and a placido ring 71. Note that the second light source 72 may be omitted. FIG. 2 shows an example of a configuration diagram of the placido ring. A Placido ring (PLACIDO'S DISC) 71 is for projecting a pattern index composed of a plurality of concentric annular zones as shown in the figure. Note that the index of a pattern composed of a plurality of concentric annular zones is an example of an index of a predetermined pattern, and other appropriate patterns can be used. And after the alignment adjustment mentioned later is completed, the parameter | index of the pattern which consists of a some concentric ring zone can be projected.
[0020]
The second light transmission optical system 80 mainly performs alignment adjustment, coordinate origin, and coordinate axis measurement / adjustment, which will be described later, for example, and includes a second light source unit 31 for emitting a light beam of the second wavelength, An optical lens 32 and a beam splitter 33 are provided.
[0021]
The second light receiving optical system 30 includes a condenser lens 34 and a second light receiving unit 35. The second light receiving optical system 30 returns a light beam (second light beam) that the pattern of the placido ring 71 illuminated from the second illumination optical system 70 is reflected and returned from the anterior eye portion or the cornea 62 of the eye 60 to be measured. And guided to the second light receiving unit 35. In addition, the light beam emitted from the second light source unit 31 and reflected from the cornea 62 of the eye 60 to be measured and returned can be guided to the second light receiving unit 35. The second wavelength of the light beam emitted from the second light source unit 31 is different from, for example, the first wavelength (here, 780 nm), and a long wavelength can be selected (for example, 940 nm).
[0022]
The common optical system 40 is disposed on the optical axis of the light beam emitted from the first illumination optical system 10, and includes the first and second illumination

optical systems

10 and 70, the first and second light receiving

optical systems

20 and 30, and the second. The optical transmission system 80 can be included in common, and includes, for example, an afocal lens 42, beam splitters 43 and 45, and a condensing lens 44. The beam splitter 43 transmits (reflects) the wavelength of the second light source unit 31 to the eye 60 to be measured and reflects the second light flux reflected and returned from the retina 61 of the eye 60 to be measured. It is formed by a mirror (for example, a polarization beam splitter) that transmits the light beam of the first light source unit 11. The beam splitter 45 transmits (reflects) the wavelength of the first light source unit 11 to the eye 60 to be measured, and transmits a first light beam reflected and returned from the retina 61 of the eye 60 to be measured (a mirror ( For example, it is formed of a dichroic mirror. The beam splitters 43 and 45 prevent the first and second light beams from entering the other optical system and causing noise.
[0023]
The adjustment optical system 50 mainly performs, for example, adjustment of a working distance described later, and includes a third light source unit 51, a fourth light source unit 55, condensing lenses 52 and 53, and a third light receiving unit 54. And mainly adjust the working distance.
[0024]
Next, alignment adjustment will be described. The alignment adjustment is mainly performed by the second light receiving optical system 30 and the second light transmitting optical system 80.
[0025]
First, the light beam from the second light source unit 31 illuminates the eye 60 to be measured, which is an object, with a substantially parallel light beam via the condenser lens 32, the beam splitters 33 and 43, and the afocal lens 42. The reflected light beam reflected by the cornea 62 of the eye 60 to be measured is emitted as a divergent light beam as if it was emitted from a point having a radius of curvature of the cornea 62. The divergent light beam is received as a spot image by the second light receiving unit 35 through the afocal lens 42, the beam splitters 43 and 33, and the condenser lens 34.
[0026]
Here, when the spot image on the second light receiving unit 35 is off the optical axis, the eye optical characteristic measuring device main body is moved and adjusted vertically and horizontally so that the spot image coincides with the optical axis. As described above, when the spot image coincides with the optical axis, the alignment adjustment is completed. In the alignment adjustment, the cornea 62 of the eye 60 to be measured is illuminated by the third light source unit 51, and an image of the eye 60 to be measured obtained by this illumination is formed on the second light receiving unit 35. May be used so that the pupil center coincides with the optical axis.
[0027]
Next, the working distance adjustment will be described. The working distance adjustment is mainly performed by the adjustment optical system 50.
First, the working distance adjustment is performed, for example, by irradiating a parallel light beam near the optical axis emitted from the fourth light source unit 55 toward the eye 60 to be measured and the light reflected from the eye 60 to be measured. This is performed by receiving light at the third light receiving unit 54 via the condenser lenses 52 and 53. Further, when the eye 60 to be measured is at an appropriate working distance, a spot image from the fourth light source unit 55 is formed on the optical axis of the third light receiving unit 54. On the other hand, when the eye 60 to be measured deviates back and forth from an appropriate working distance, the spot image from the fourth light source unit 55 is formed above or below the optical axis of the third light receiving unit 54. The third light receiving unit 54 only needs to be able to detect a change in the position of the light beam in the plane including the fourth light source unit 55, the optical axis, and the third light receiving unit 54. For example, the one-dimensionally arranged in this plane A CCD, a position sensing device (PSD), etc. can be applied.
[0028]
Next, the positional relationship between the first illumination optical system 10 and the first light receiving optical system 20 will be schematically described.
A beam splitter 45 is inserted into the first light receiving optical system 20, and the light from the first illumination optical system 10 is transmitted to the eye to be measured 60 by the beam splitter 45 and the eye to be measured 60. The reflected light from is transmitted. The first light receiving unit 23 included in the first light receiving optical system 20 receives light that has passed through the Hartmann plate 22 that is a conversion member, and generates a light reception signal.
[0029]
Further, the first light source unit 11 and the retina 61 of the eye 60 to be measured form a conjugate relationship. The retina 61 of the eye 60 to be measured and the first light receiving unit 23 are conjugate. The Hartmann plate 22 and the pupil of the eye 60 to be measured form a conjugate relationship. Further, the first light receiving optical system 20 forms a substantially conjugate relationship with the cornea 62 and the pupil, which are the anterior segment of the eye 60 to be measured, and the Hartmann plate 22. That is, the anterior focal point of the afocal lens 42 substantially coincides with the cornea 62 and the pupil, which are the anterior segment of the eye 60 to be measured. Further, the surface of the rotary prism 16 inclined with respect to the optical axis is disposed at a position substantially conjugate with the pupil.
[0030]
In addition, the first illumination optical system 10 and the first light receiving optical system 20 assume that the light flux from the first light source unit 11 is reflected at the point where the light is collected, and the signal peak due to the reflected light from the first light receiving unit 23 is generated. Move in tandem to maximize. Specifically, the first illumination optical system 10 and the first light receiving optical system 20 move in a direction in which the signal peak at the first light receiving unit 23 increases, and stop at a position where the signal peak becomes maximum. Thereby, the light beam from the first light source unit 11 is collected on the eye 60 to be measured.
[0031]
The lens 12 converts the diffused light from the light source 11 into parallel light. The diaphragm 14 is optically conjugate with the pupil of the eye or the Hartmann plate 21. The diaphragm 14 has a diameter smaller than the effective range of the Hartmann plate 21 so that so-called single-pass aberration measurement (a method in which the eye aberration affects only the light receiving side) is established. In order to satisfy the above, the lens 13 is disposed so that the fundus conjugate point of the actual light ray is at the front focal position, and further, the rear focal position is coincident with the stop 14 in order to satisfy the conjugate relationship with the eye pupil. ing.
[0032]
The light beam 15 travels in the same manner as the light beam 24 in a paraxial manner after the light beam 24 and the beam splitter 45 have a common optical path. However, in the single pass measurement, the diameters of the respective light beams are different, and the beam diameter of the light beam 15 is set to be considerably smaller than that of the light beam 24. Specifically, the beam diameter of the light beam 15 may be, for example, about 1 mm at the pupil position of the eye, and the beam diameter of the light beam 24 may be about 7 mm (in the drawing, from the beam splitter 45 of the light beam 15 to the fundus). 61 is omitted).
[0033]
Next, the Hartmann plate 22 as a conversion member will be described.
The Hartmann plate 22 included in the first light receiving optical system 20 is a wavefront conversion member that converts a reflected light beam into a plurality of beams. Here, a plurality of micro Fresnel lenses arranged in a plane orthogonal to the optical axis is applied to the Hartmann plate 22. In general, in order to measure the spherical component, third-order astigmatism, and other higher-order aberrations of the measurement target portion 60 (measured eye 60), at least via the measured eye 60. It is necessary to measure with 17 beams.
[0034]
The micro Fresnel lens is an optical element, and includes, for example, an annular zone having a height pitch for each wavelength and a blaze optimized for emission parallel to the focal point. The micro Fresnel lens here is, for example, an optical path length difference of 8 levels applying a semiconductor microfabrication technique, and achieves a high light collection rate (for example, 98%).
[0035]
The reflected light from the retina 61 of the eye 60 to be measured passes through the afocal lens 42 and the collimating lens 21 and is condensed on the first light receiving unit 23 via the Hartmann plate 22. Therefore, the Hartmann plate 22 includes a wavefront conversion member that converts the reflected light beam into at least 17 beams.
[0036]
FIG. 3 is a block diagram showing a schematic electrical system 200 of the eye optical property measuring apparatus according to the present invention. The electrical system 200 related to the ophthalmic optical characteristic measurement apparatus includes, for example, a calculation unit 210, a control unit 220, a display unit 230, a memory 240, a first drive unit 250, and a second drive unit.
[0037]
The calculation unit 210 receives the light receiving signal obtained from the first light receiving unit 23. (4) , A light receiving signal obtained from the second light receiving unit 35 (7) In addition to receiving the light reception signal (10) obtained from the third light receiving unit 54, the coordinate origin, coordinate axis, coordinate movement, rotation, total wavefront aberration, cornea is surface aberration, Zernike coefficient, aberration coefficient, Strehl ratio, white light MTF, Landolt ring pattern, etc. are calculated. In addition, signals according to such calculation results are output to the control unit 220 that controls the entire electric drive system, the display unit 230, and the memory 240, respectively. Details of the operation 210 will be described later.
[0038]
The control unit 220 controls turning on and off of the first light source unit 11 based on a control signal from the calculation unit 210, and controls the first driving unit 250 and the second driving unit 260. A signal is sent to the first light source unit 11 based on a signal corresponding to a calculation result in the calculation unit 210. (1) Is output to the platide ring 71. (5) Is output to the second light source unit 31. (6) Is output to the third light source unit 51. (8) Is output to the fourth drive unit (9) In addition, a signal is output to the first driving unit 250 and the second driving unit 260.
[0039]
For example, the first driving unit 250 receives a light reception signal from the first light receiving unit 23 input to the calculation unit 210. (4) The first illumination optical system 10 as a whole is moved in the direction of the optical axis based on the (2) And the lens moving means is driven. As a result, the first drive unit 250 can move and adjust the first illumination optical system 10.
[0040]
The second driving means 260 is, for example, a light reception signal from the first light receiving unit 23 input to the calculation unit 210. (4) The entire first light receiving optical system 20 is moved in the optical axis direction based on the (3) And the lens moving means is driven. As a result, the second driving unit 260 can move and adjust the first light receiving optical system 20.
[0041]
In FIG. 4, the detailed block diagram regarding the calculating part of the eye characteristic measuring apparatus of this invention is shown. The calculation unit 210 includes a measurement unit 111, an analysis unit 111 ′, a coordinate setting unit 112, an alignment control unit 113, a marker setting unit 114, an input / output unit 115, and a conversion unit 116.
[0042]
The first light receiving unit 23 forms a first received light signal from the received light beam reflected from the fundus of the eye to be examined and returns it to the measuring unit 111. The second light receiving unit 35 forms a second received light signal including information on the anterior ocular segment from a received light beam including information on a characteristic portion of the anterior eye portion to be examined and / or a marker formed on the anterior eye portion to be examined. Guide to the measuring unit 111 and the coordinate setting unit 112.
[0043]
The measuring unit 111 obtains optical characteristics including the refractive power of the eye to be examined or the formation of the cornea based on the first light receiving signal from the first light receiving unit. In addition, the measurement unit 111 sends a first light reception signal to the analysis unit 111 ′ for obtaining the spot diameter of the received light beam and the degree of scattering of the received light beam. The analysis unit 111 ′ may be configured to directly input the first light reception signal from the first light reception unit 23. Details of the analysis unit 111 ′ will be described later. In particular, the measurement unit 111 performs eye optical characteristic measurement based on the first light reception signal from the first light reception unit 23. In addition, the measurement unit 111 performs corneal topography measurement based on the second light reception signal from the second light reception unit 35 in particular. In addition, the measurement unit 111 calculates an aberration result, calculates an ablation amount as necessary, and outputs the calculation result to the surgical apparatus via the input / output unit 115.
[0044]
FIG. 5 is an enlarged view of a part of the image received by the first light receiving unit 23. (A) is an example of a Hartmann image in the case of a keratoconic eye and (B) is a cataract eye. The Hartmann image received by the first light receiving unit 23 is, for example, an image based on the reflected light from the eye to be measured, and the first received light is a light beam that is substantially diffused outward through the Hartmann plate 22. A plurality of region points (in the figure, circular, elliptical, etc.) when light is received on the portion 23 are included. The optical signal of the Hartmann image in this example is converted into an electric signal and input (or taken in) to the analysis unit 111 ′ as the first signal.
[0045]
Thus, information from the Hartmann Shack wavefront sensor includes the following.
・ Wavefront from the center of gravity of point image (classical aberration measurement)
・ Local information (local scattering measurement)
For eyes with much scattering, blurring of an image that cannot be explained only by wavefront aberration is observed in the Hartmann image. It is also conceivable to estimate the amount of scattering by comparing a Hartmann image obtained by measurement with a Hartmann image restored from wavefront aberration.
[0046]
In the analysis unit 111 ′, the plurality of region points are regarded as one of the received light beams, and the ratio between the spot diameter of the received light beam or the maximum value and the minimum value of the light amount of the received light beam, that is, the degree of scattering of the received light beam is obtained. The analysis unit 111 ′ obtains a distribution indicating the relationship between the wavefront aberration of the light beam incident on the light receiving optical system and the degree of scattering of the light received light beam. Further, a distribution indicating the relationship between the wavefront aberration of the light beam incident on the light receiving optical system and the spot diameter of the light received light beam is obtained. The analysis unit 111 ′ obtains a distribution regarding the correlation between the wavefront aberration of the light beam incident on the light receiving optical system, the degree of scattering of the light received light beam, and the spot diameter of the light received light beam, and is not limited to the above-described distribution. .
[0047]
The analysis unit 111 ′ obtains a point image intensity distribution (PSF) by wave optical calculation from the wavefront aberration of the light beam incident on the light receiving optical system, and measures the diameter of the received light beam, that is, the intensity from the image. It has a calculation function for comparing the obtained point image intensity distribution (PSF). For example, the area at the intermediate value between the maximum and minimum values in a square area containing point images (the length of the side is approximately equal to the interval between the point images, and this area usually contains one point image) Or you may be able to compare widths.
The analysis described so far by the analysis unit 111 ′ may correspond to a specific plurality of point images of the Hartmann image. Under this condition, as a result of one measurement, the calculation is performed for each point. An average value of values obtained by analyzing an image or actually measured may be used.
The analysis unit 111 ′ determines that there is an influence of cataract or the like as the degree of scattering of the received light beam of the light beam incident on the light receiving optical system that is the first light receiving unit is larger, and the display unit 240 displays that effect. Can be output. Further, the analysis unit 111 ′ determines that the larger the spot diameter of the received light flux in the received light receiving optical system that is the first light receiving unit, the greater the influence of cataracts, and outputs that effect to the display unit 240. be able to.
[0048]
The determination result, analysis result, and the like by the analysis unit 111 ′ are displayed on the display unit 240 in various formats such as data, table, graph, three-dimensional display, graphic display, and the output unit displays CD-ROM, FD, MO. It may be outputted to a recording medium such as
FIG. 6 is an explanatory diagram for obtaining the point image intensity distribution from the wavefront.
The wavefront of the light beam reflected from the fundus of the eye to be examined passes through the Hartmann plate, and the wavefront aberration RMS in the lenslet is obtained from the inclination of the light beam at that time, and factors such as the area of the half-value portion of the point image intensity distribution PSF are obtained.
The analysis unit 111 ′ can obtain the scattering coefficient as the following equation.
[0049]
[Expression 1]

[0050]
Index: Scattering coefficient (also called scattering index)
A: Area of half-value part of PSF (average)
・ RMS _SL : Wavefront aberration at lenslet (average)
・ A: Constant obtained by non-cataract eye measurement
C: Scattering calibration constant of the measuring device
Note that a and c are regression line coefficients obtained in FIG. 7 using the keratoconic eye and the normal eye. In this case, a: first order coefficient is 28.894, c: constant term is 8.6623.
In the actual analysis, the area A is obtained for a plurality of point images of the Hartmann image, and this is processed by the above formula, and may be averaged as a result of one measurement.
This scattering coefficient is obtained for each lenslet using various factors of each lenslet.
The relationship between the point image and the point image intensity is as shown in FIG. At this time, if a CCD having a gamma value of 1 indicating the relationship between the amount of light and the output is employed, the intensity distribution of the PSF is proportional to the digital count (computer count) of the CCD, so measurement is simple. Here, without the square of 0.6mm square centering on the point image, the minimum and maximum strengths are obtained. Michael It is also possible to obtain the Soncon contrast ratio, and it is also possible to obtain the area of the midpoint between the lowest and highest intensity.
Wavefront aberration RMS _SL Instead of the above, it is also conceivable to calculate the point image intensity distribution (PSF) in FIG. 6 from the wavefront aberration and compare it with the actually measured PSF.
Using this method eliminates the need for calibration using less scatter eyes such as normal eyes and keratoconus, increasing the reliability of the results. On the other hand, in the method before comparing the wavefront aberration and the PSF, there is no need to calculate the PSF by calculation, so that the entire processing time can be considerably shortened.
[0051]
The coordinate setting unit 112 converts the signals of the first and second coordinate systems corresponding to the eye to be examined included in the first or second light reception signal into signals of the reference coordinate system, respectively. The coordinate setting unit 112 obtains a pupil edge and a pupil center based on each signal of the first and second coordinate systems.
[0052]
In addition, the coordinate setting unit 112 determines the coordinate origin and the direction of the coordinate axis based on the second received light signal including the characteristic signal of the anterior eye portion to be examined. In addition, the coordinate setting unit 112 obtains the coordinate origin and the rotation and movement of the coordinate axis based on at least one of the characteristic signals of the anterior segment of the eye to be examined in the second received light signal, and associates the measurement data with the coordinate axis. Do. The characteristic portion includes at least one of a pupil position, a pupil center, a cornea center, an iris position, an iris pattern, a pupil shape, and a limbus shape. For example, the coordinate setting unit 112 sets coordinate origins such as the pupil center and the cornea center. The coordinate setting unit 112 forms a coordinate system based on the feature signal corresponding to the image of the feature portion of the anterior eye portion to be examined included in the second light reception signal. The coordinate setting unit 112 forms a coordinate system based on the marker signal for the marker provided on the eye to be examined and the signal for the anterior eye part to be examined, which are included in the second light receiving signal. The coordinate setting unit 112 can determine the coordinate origin and the direction of the coordinate axis based on the second light receiving signal including the marker signal. The coordinate setting unit 112 obtains the coordinate origin based on the marker signal in the second light reception signal, and rotates the coordinate axis based on at least one of the characteristic signals of the anterior eye segment in the second light reception signal. The movement can be obtained, and the relationship between the measurement data and the coordinates can be performed. Alternatively, the coordinate setting unit 112 obtains the coordinate origin based on at least one of the feature signals for the anterior segment in the second light reception signal, and rotates or moves the coordinate axis based on the marker signal in the second light reception signal. And the correlation between the measurement data and the coordinate axes may be performed. Alternatively, the coordinate setting unit 112 obtains the coordinate origin and the rotation and movement of the coordinate axis based on at least one of the characteristic signals of the anterior segment of the eye to be examined in the second light reception signal, and associates the measurement data with the coordinate axis. You may make it perform.
[0053]
The conversion unit 116 synthesizes the first and second optical characteristics of the eye to be examined obtained by the measurement unit 111 in relation to each reference coordinate system formed by the coordinate setting unit. The conversion unit 116 converts the pupil center obtained by the coordinate setting unit 112 into the reference coordinate system by using the origin as the origin.
[0054]
The first illumination optical system, the first light receiving optical system 20, the second light receiving optical system 30, the common optical system 40, the adjusting optical system 50, the second illumination optical system 70, and the second light transmitting optical system Any one or plural or all of 80 and the like are appropriately listed in the alignment unit of the optical system 100. The alignment control unit 113 enables the alignment unit to move according to the movement of the eye to be examined, according to the calculation result of the coordinate setting unit 112 based on the second light receiving signal obtained by the second light receiving unit. Based on the coordinate system set by the coordinate setting unit 112, the marker setting unit 114 forms a marker associated with this coordinate system in the anterior eye portion to be examined. The input / output unit 115 is an interface for outputting data such as an aberration amount, coordinate origin, coordinate axis rotation, movement, and ablation amount and calculation results from the measurement unit or coordinate setting unit to the surgical apparatus. The display unit 240 displays the optical characteristics of the eye to be examined obtained by the measuring unit 111 in relation to the coordinate system formed by the coordinate setting unit.
[0055]
The surgical apparatus 300 includes a surgical control unit 121, a processing unit 122, and a memory unit 123. The surgery control unit 121 controls the processing unit 122 to control surgery such as corneal cutting. The processing unit 122 includes a laser for surgery such as corneal cutting. The operation memory unit 123 stores data for operations such as data related to cutting, monograms, and operation plans.
[0056]
Next, FIG. 7 shows a diagram (1) of an experimental result by the eye optical characteristic measuring apparatus according to the present embodiment. In the embodiment of the present invention, in order to confirm the measurement of the ocular optical characteristics, nine normal eyes, 24 keratoconic eyes, and 17 cataract eyes were measured, and the half width was obtained. In the figure, normal eyes are indicated by rhombuses (♦), keratoconus eyes are indicated by squares (■), and cataract eyes are indicated by triangles (▲).
[0057]
The measurement unit 111 or the analysis unit 111 ′ receives the first light reception signal. (4) The output result from is analyzed by a predetermined analysis method. That is, the blur of the received laser beam is considered as scattered light, and the half width based on the spot diameter of the received light beam (square root of area for spots) or the ratio of the minimum received light amount to the maximum received light amount of the received light beam That is, a scattering intensity ratio (minimum intensity / maximum intensity, scattering coefficient) is obtained. In addition, the measuring unit 111 or the analyzing unit 111 ′ receives the spot diameter distribution (FIG. 6) or received light of the received light beam with respect to the phase (standard deviation) of the wavefront aberration incident on the first light receiving unit 23 obtained by the light receiving optical system. Create a distribution of the scattered light intensity ratio.
[0058]
In addition, about the cataract eye, it can distinguish and distinguish from the keratoconus eye by deviating from this approximated straight line. That is, it is possible to discriminate a subject suspected of having a cataract eye based on the obtained linear approximation and use it as a judgment material for surgery / treatment.
[0059]
FIG. 8 shows a diagram (2) of an experimental result by the eye optical characteristic measuring apparatus according to the present embodiment.
This figure is obtained by adding correction by [Equation 1] from the half-value width of FIG. The vertical axis represents the amount obtained by subtracting the value obtained by substituting the wavefront aberration of the lenslet into [Equation 1] from the half width. For non-cataract eyes, the calculated values are almost side by side. This value is large for cataract eyes or eyes with large scattering. It is also conceivable to measure a model eye that can ignore scattering, and further calibrate with this measured value to make the prediction of the amount of scattering more accurate. Here, the method used is suitable for the measurement of lens scattering, but it can also be applied to the measurement of retinal scattering and the like.
[0060]
As a result of the analysis, for example, SIR (scattering intensity ratio) = 0.460 ± 0.067 in normal eyes, SIR = 0.495 ± 0.098 in keratoconic eyes, and SIR = 0.667 ± 0. 148 (ANOVA (ANOVA), P <0.01). The scattering coefficient was 2.61 ± 0.70 for normal eyes, 3.38 ± 2.73 for keratoconic eyes, and 10.13 ± 7.25 for cataract eyes. Further, there was no significant difference between normal eyes and keratoconus eyes (P <0.122), but there was significant difference between normal eyes and cataract eyes, and between corneal eyes and cataract eyes (P <0). .01). In order to confirm the effectiveness of the analysis method, nine normal eyes with low scattering, 24 corneal eyes with 24 scatters, and 17 cataract eyes with large scatter were measured.
[0061]
This suggests the possibility of measuring the amount of scattering by the Hartmann Shack wavefront sensor. In the future, we will examine evaluation criteria comparable to visual function and confirm clinical effectiveness.
[Industrial applicability]
[0062]
According to the present invention, it is possible to provide an ophthalmic optical characteristic measuring apparatus that enables scatter measurement with a Hartmann Shack wavefront sensor, whose main purpose is wavefront aberration measurement, and can accurately evaluate visual function by performing scatter measurement.
[0063]
In addition, according to the present invention, a scattering analysis method for estimating the amount of scattering from a scattering intensity ratio (SIR) of a background light of a Hartmann image has been newly developed as a scattering measurement method using a Hartmann Shack wavefront sensor. It is possible to provide an eye optical property measuring apparatus that enables simultaneous measurement of scattering by an optical system of a wavefront sensor.
[0064]
Further, according to the present invention, from the distribution of the relationship between the wavefront aberration of the light beam incident on the light receiving optical system and the degree of scattering of the light received light beam, the wavefront aberration of the light beam incident on the light receiving optical system and the degree of scattering of the received light beam become stronger. Thus, it is possible to provide an ophthalmic optical characteristic measuring apparatus that can be determined to have an effect of cataract.
Further, according to the present invention, from the distribution of the relationship between the wavefront aberration of the light beam incident on the light receiving optical system, the degree of scattering of the light received light beam, and the spot diameter of the received light beam, the wavefront aberration of the light beam incident on the light receiving optical system, It is possible to provide an ophthalmic optical characteristic measuring apparatus that can determine that the influence of cataract is greater as the degree of scattering of the received light beam is stronger or the spot diameter of the received light beam is larger.
[Brief description of the drawings]
[0065]
FIG. 1 is a diagram showing a schematic optical system 100 of an eye optical characteristic measuring apparatus according to the present invention.
FIG. 2 is a configuration diagram of a placido ring.
FIG. 3 is a block diagram showing a schematic electrical system 200 of the eye optical characteristic measurement apparatus according to the present invention.
FIG. 4 is a detailed configuration diagram relating to a calculation unit of the eye characteristic measuring apparatus according to the present invention.
5 is an enlarged view of a part of an image received by a first light receiving unit 23. FIG.
FIG. 6 is an explanatory diagram for obtaining a point image intensity distribution from a wavefront.
FIG. 7 is a diagram (1) of an experimental result by the eye optical property measurement apparatus according to the present embodiment.
FIG. 8 is a diagram (2) of an experimental result by the eye optical property measurement apparatus according to the present embodiment.
FIG. 9 is an explanatory diagram showing a point image and a point image intensity.

Claims

A light source that emits a light beam of a predetermined wavelength;
An illumination optical system for illuminating a minute region on the retina of the eye to be inspected with a light beam from the light source unit;
A light receiving optical system for receiving a part of the reflected light beam reflected from the retina of the eye to be examined through a conversion member that converts the light beam from the light source unit into at least substantially 17 beams;
A light receiving portion for receiving a received light beam guided by the light receiving optical system and forming a signal;
An eye optical specific measurement device comprising: a calculation unit that obtains wavefront aberration of a light beam incident on the light receiving optical system and a degree of scattering of the received light beam based on a signal from the light receiving unit.

A light source that emits a light beam of a predetermined wavelength;
An illumination optical system for illuminating a minute region on the retina of the eye to be inspected with a light beam from the light source unit;
A light receiving optical system for receiving a part of the reflected light beam reflected from the retina of the eye to be examined through a conversion member that converts the light beam from the light source unit into at least substantially 17 beams;
A light receiving portion for receiving a received light beam guided by the light receiving optical system and forming a signal;
An eye optical specific measurement apparatus comprising: a calculation unit that obtains a wavefront aberration of a light beam incident on the light receiving optical system and a spot diameter of the received light beam based on a signal from the light receiving unit.

The ophthalmic optical characteristic measuring device according to claim 1.
The ophthalmic optical characteristic measuring apparatus, wherein the calculation unit obtains a distribution of a relationship between a wavefront aberration of a light beam incident on the light receiving optical system and a degree of scattering of the light received light beam.

The ophthalmic optical characteristic measuring apparatus according to claim 3.
The ophthalmic optical characteristic measuring apparatus, wherein the calculation unit is configured to determine that the greater the degree of scattering of the received light beam, the more affected by cataract.

The ophthalmic optical characteristic measuring apparatus according to claim 2.
The apparatus for measuring optical characteristics of an eye, wherein the calculation unit obtains a distribution of a relationship between a wavefront aberration of a light beam incident on the light receiving optical system and a spot diameter of the light received light beam.

The ophthalmic optical characteristic measuring apparatus according to claim 2.
An ophthalmic optical characteristic measuring apparatus that predicts lens scattering and retinal scattering by subtracting the influence of wavefront aberration from the obtained spot diameter of the received light beam.

The ophthalmic optical characteristic measuring apparatus according to claim 2.
In order to subtract the effect of wavefront aberration from the calculated spot diameter of received light flux, an approximate straight line based on the measured spot diameter and wavefront aberration of non-cataract eyes such as normal eyes and keratoconus eyes is used. Then, an eye optical property measuring apparatus that predicts lens scattering and retinal scattering.

The ophthalmic optical characteristic measuring apparatus according to claim 2.
In order to subtract the influence of wavefront aberration from the spot diameter of the received light flux, the approximate straight line based on the measured spot diameter of the received light flux and the wavefront aberration of a non-cataract eye such as a normal eye or a keratoconus eye, Further, an ophthalmic optical characteristic measuring apparatus which corrects based on a model eye measurement value in order to constitute a scattering amount of the apparatus itself and predicts lens scattering and retinal scattering.

The apparatus for measuring optical characteristics of an eye according to claim 5.
The ophthalmic optical characteristic measuring apparatus, wherein the arithmetic unit is configured to determine that the larger the spot diameter of the received light beam is, the more affected by cataracts.

The ophthalmic optical characteristic measuring device according to claim 1.
The ophthalmic optical characteristic measuring apparatus, wherein the calculation unit obtains a distribution of a relationship among a wavefront aberration of a light beam incident on the light receiving optical system, a degree of scattering of the received light beam, and a spot diameter of the received light beam.

The ophthalmic optical characteristic measuring device according to claim 10.
The calculation unit determines that the greater the wavefront aberration of the light beam incident on the received light receiving optical system and the degree of scattering of the received light beam, or the larger the spot diameter of the received light beam, the greater the influence of cataracts. An ophthalmic optical characteristic measuring apparatus configured as described above.

The ophthalmic optical characteristic measuring device according to claim 3 to 11,
An ophthalmic optical characteristic measuring apparatus further comprising a display unit that displays the distribution obtained by the arithmetic unit.

The ophthalmic optical characteristic measuring device according to claim 4, 9 or 11,
An ophthalmic optical characteristic measuring apparatus further comprising a display unit or an output unit that displays or outputs a determination result by the arithmetic unit.

A light source that emits a light beam of a predetermined wavelength;
An illumination optical system for illuminating a minute region on the eye retina with the light flux from the light source unit;
A light receiving optical system for receiving a part of the reflected light beam reflected from the retina of the eye to be examined through a conversion member that converts the light beam from the light source unit into at least substantially 17 beams;
A light receiving portion for receiving a received light beam guided by the light receiving optical system and forming a signal;
An ophthalmic optical characteristic measuring apparatus comprising: a point image intensity distribution obtained from wavefront aberration of a light beam incident on the light receiving optical system based on a signal from the light receiving unit; and a calculation unit for obtaining an actually measured spot diameter of the received light beam. .

The ophthalmic optical characteristic measuring device according to claim 14,
The arithmetic unit, the light receiving and point image intensity distribution obtained from the wavefront aberration of the light beam incident to the optical system, the eye's optical characteristic measuring apparatus characterized by determining the distribution of the relationship of the scattering degree of the received light flux.

The ophthalmic optical characteristic measuring device according to claim 14,
The optical unit is configured to determine that the larger the obtained point image intensity distribution diameter and / or spot diameter of the received light beam is, the more affected by cataracts, etc. Characteristic measuring device.

The ophthalmic optical characteristic measuring device according to claim 14,
An eye optical characteristic measuring apparatus characterized in that the calculation unit obtains a distribution of a relationship between a diameter of a point image intensity distribution obtained from a wavefront aberration of a light beam incident on the light receiving optical system and a spot diameter of the light received light beam. .

The ophthalmic optical characteristic measuring device according to claim 14,
An eye optical characteristic measuring apparatus for predicting lens scattering and retinal scattering by subtracting the diameter of the point image intensity distribution from the spot diameter of the received light flux.

The ophthalmic optical characteristic measuring apparatus according to claim 2.
The calculation unit obtains a point image intensity distribution (PSF) obtained based on a signal from the light receiving unit, and a point obtained from the obtained point image intensity distribution and the wavefront aberration of the eye to be examined based on the signal from the light receiving unit. An eye optical characteristic measuring device characterized by predicting lens scattering and retinal scattering by comparing image intensity distributions.

The ophthalmic optical characteristic measuring apparatus according to claim 2.
The above calculation unit calculates the minimum and maximum intensities in a predetermined range centered on the point image, and based on this, calculates the Michelson contrast ratio or the area of the midpoint between the minimum and maximum intensities, and predicts lens scattering and retinal scattering. An eye optical characteristic measuring apparatus.